Abstract
Agarose hydrogels are poroviscoelastic materials that exhibit a waterlogged-crosslinked microstructure. Despite an extensive use in biotechnologies and numerous studies of the elastic properties of agarose gels, little is known about the compressible behavior and the microstructural changes of such fibrillar hydrogels under compression. The present work investigates the mechanical response of centimeter-sized pre-molded agarose cylinders when applying a compressive strain ramp over an extended range of loading speed and polymer concentration. One of the original contributions is the simultaneous monitoring of the changes in the hydrogel volume to determine the Poisson’s ratio through a spatiotemporal method. The linear poroelastic response of agarose hydrogels shows a compressible behavior at strain rates less than 0.7 % s−1. The critical compressive strain of a few percent at the onset of the non-linear regime and the always positive Poisson’s ratio decrease when applying a slow compressive ramp. The mechanical response in the linear regime is typical of a deformation mode either dominated by the bending of semiflexible strands (enthalpic regime) or by the stretching of the network (entropic regime) at higher agarose concentration. Cyclic linear shear deformations superimposed to a compressive strain from 0.5 up to 40% further give evidence of a compression-softening of the network causing the transition to the non-linear regime without dependence upon the network topology and connectivity. Finally, the buckling-induced aging of the network under a weak compression and the poroviscoelasticity of the hydrogel are shown to impact the relaxation of the normal stress and the equilibrium stress.
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Notes
The equilibrium height ho of the pre-molded gel is slightly less than the height H of the duralumin mold as the sol-gel transition induces a small water release and a volume retraction of the sample as reported by Mao et al. (2016). Here, the hydrogel under tension in the mold at room temperature undergoes a uniform spontaneous shrinkage when demolding the cylinder with an equilibrium contraction ratio χ = (H − ho)/H which increases linearly with the polymer concentration and reaches a plateau value χ = (3.1 ± 0.2) % at agarose mass concentrations c > 1.5 wt%.
Note that the slow compression of the L3 hydrogel in air causes an early exudation of water from the outer free surface (third column in Fig. 5) and an apparent slight increase in the rate of swelling of the cylinder with a consequent overestimation of the Poisson's ratio as determined by the spatiotemporal method.
The deformation of the agarose hydrogel appears as reversible after a fast or a slow 15 % compressive strain ramp and the material nearly recovers the initial shape within half an hour when removing the load. The hydrogel can further be compressed up to a 90% strain without breaking under an extremely low loading speed dh/dt = 0.1μm/s (dε/dt ≈ 7.1 10−4 % s−1) at agarose concentrations from 0.5 wt% up to 12 wt% as previously reported for gellan gels for polymer concentrations 0.81 wt% < c < 2.5 wt% (Nakamura et al. 2001).
For highly diluted agarose and biopolymer hydrogels close to the percolation threshold (ϕg ≈ 0.1% < ϕ < 0.5%), experimental values of the elastic exponent β are quite dispersed in the range from 1.8 up to 4 (Tokita and Hikichi 1987; Clark and Ross-Murphy 1987; Kawabata et al. 1996; Mohammed et al. 1998; Fujii et al. 2000; Gunasekaran and Yoon 2014). Considering agarose fibers as stiff linear rods, the scalar percolation theory from de Gennes (1980) gives a critical exponent β ≈ 1.9 (Djabourov 1991). On the other hand, a vectorial percolation model taking into account the bending of fibers predicts a higher value β ≈ 3.96 of the elastic exponent (Sahimi 1986). However, the dispersion in the experimental values of the scaling exponent in the close vicinity of the gel point also arises both from loose chains (free chains) that gradually vanish upon increasing the agarose concentration and from a greater sensitivity of the hydrogel elasticity to the molecular weight distribution of the polymer.
One strand of length ξ and cross section r2 in a volume of size ξ corresponds to a fiber volume fraction ϕ - ϕg ∝ r2ξ/ξ3 = r2/ξ2 and a mesh size ξ ∝ r (ϕ - ϕg)λ) with a scaling exponent λ = − 1/2. The scaling relation ξ ∝ (ϕ - ϕg)-1/2 describes the concentration dependence of the pore diameter in agarose hydrogels both for the larger and the smaller free spaces at fiber volume fraction ϕ < 3 wt% (Fig. 16in Appendix 5.1).
The typical mesh size of concentrated agarose hydrogels scales as ξ ∝ εc ∝ (ϕ - ϕg)-0.45 with a scaling exponent λ ≈ − 0.45 less than the expected value λ = − 0.5 for a sparse semiflexible network since the radius r of strands is no longer small enough compared to the mean diameter ξ of pores.
The forced permeation time t* ∝ η R2/(E k) of a solvent through a semiflexible hydrogel under compression scales as the square of the cylinder radius R and as the inverse of the elastic modulus E of the soft material where k ∝ ξ2 is the hydraulic permeability of the network and η the viscosity of the solvent (Doi 2009).
A minimum compressive strain ε = 4% is required for an accurate determination of the drained Poisson’s ratio using the spatiotemporal method.
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Acknowledgements
The authors gratefully acknowledge M Benelmostafa for stimulating discussions, D Dahmani for supplying the Setexam agarose, the expertise center PLACAMAT in Talence (France) for the Cryo-SEM observations and B Mao (BioMérieux Craponne) for the molecular weight characterization of agarose samples by size exclusion chromatography.
Funding
This work was supported by annual funding from the CNRS (Centre National de la Recherche Scientifique) in France and the University Mohammed Premier in Oujda (Morocco).
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Appendix
Appendix
Mean pore diameter of agarose hydrogels
Cryo-SEM micrographs of agarose hydrogels show random fibrillar networks with a typical mean pore diameter d decreasing with the mass concentration of the polymer from a micrometer size at c ≈ 0.3 wt% down to a few hundreds of nanometers at c ≈ 3 wt% (Fig. 2). The pore size distribution is broad with a factor of about 10 between the mean smaller diameter dmin and the mean larger diameter dmax of pores in the network (full black and red circles in Fig. 16). Mechanical-scanning probe microscopy indeed gives evidence of the inhomogeneous microstructure of agarose hydrogels at low concentrations 0.5 wt % < c < 2 wt% with a log-normal distribution of the local shear modulus, while a simple Gaussian distribution describes the histogram of local elastic moduli values in thermal gels made of flexible chains such as polyacrylamide (Nitta et al. 2003). As expected for a fibrillar semiflexible network with a mesh size larger than the strand diameter, the mean pore diameter of agarose hydrogels scales as (c − cg)λ with λ ≈ − 0.5 at 0.3 wt% < c < 3 wt% whatever one considers either the larger or the smaller free spaces (Fig. 16). Note that the scaling exponent λ ≈ − 0.5 takes slightly more negative values when considering the mass concentration in place of the deviation concentration c − cg from the percolation threshold (Maaloum et al. 1998; Righetti et al. 1981). Atomic force microscopic observations from Maaloum et al. (1998) or studies of the electrophoretic mobility of latex particles in agarose hydrogels from Righetti et al. (1981) indeed lead to a similar scaling exponent λ ≈ − 0.5 provided that the mean pore diameter is plotted versus the deviation concentration c − cg from the percolation point (Fig. 16). The length scale explored in sparsely connected networks is further very sensitive to the choice of the investigation method due to the broad pore size distribution of biopolymer hydrogels.
Compression–tension of agarose hydrogels
The reversibility of the hydrogel response is studied by applying a compression–tension cycle at a speed dh/dt = 100 µm/s with a maximum compressive strain εm of either 2% (black curves in Fig. 17) or 10% (red curves in Fig. 17). The stress–strain response appears as nearly reversible in the linear regime for a maximum compressive εm ≈ 2% less than the critical strain εc as water exudation remains negligible during a fast compression–tension cycle (black curves in Fig. 17). A more detailed examination of σ(ε) curves nevertheless shows a weak hysteresis and a slope (dσ/dε)(ε = εm) less important at the end of the compressive ramp compared to the beginning of the tension ramp, especially at low agarose concentration (L1 sample in Fig. 17a). The asymmetry observed in the response of agarose hydrogels to a compression–tension cycle in the linear regime likely results from the deformation mode of strands since it is easier to bend a fiber during compression than to stretch the fiber during extension.
As expected, the hysteresis becomes more significant in the non-linear regime for a maximum compressive strain εm ≈10 % > εc (full red lines in Fig. 17) as the unbuckling of strands and the breaking of some weak bonds require longer timescales during the extension phase. The degree of hysteresis increases somewhat with the polymer concentration (Fig. 17), and the gel cylinder almost recovers the initial height ho ≈14 mm after a time period from a few minutes to a few hours when removing the load which confirms the dominant elastic behavior of agarose hydrogels. The compression-softening of the fibrillar network thus appears as nearly reversible even for very large compressive strain at very low loading speed as long as the hydrogel remains intact without any stress-induced microfractures. A second compression–tension cycle is necessary to observe a fully reversible deformation of the agarose hydrogel (data not shown) likely as a result of the formation of some extra irreversible bonds between buckled strands during the first compression ramp (paper in preparation).
Agarose molecular weight and elasticity of agarose hydrogels
Compression experiments were performed using the Brookfield texture analyzer and agarose hydrogels prepared at different concentrations 0.5 wt% ≤ c ≤ 9 wt% with two different powders supplied either by Setexam or Sigma (Section 2.1). The stress–strain curves of Sigma and Setexam agarose hydrogels considered as incompressible when applying a fast 15% strain ramp at a loading speed dh/dt = 100 µm/s exhibit similar features (Figs. 10a and 18a). As expected, the agarose average molecular weight weakly influences the scaling exponents β ≈ 2.15 ± 0.05 or β ≈ 1.36 ‐ 1.41 representative of either the enthalpic or the entropic elasticity (Fig. 18b). However, Fig. 18b gives evidence of higher values of the Young modulus Eo of Sigma agarose hydrogels (Mw ≈ 3.05 105 g/mol) compared to that of Setexam agarose hydrogels (Mw ≈ 1.88 105 g/mol) regardless of the agarose concentration. The power law fits of the fiber volume fraction dependence of the Young modulus Eo(ϕ - ϕg) of Sigma and agarose hydrogels in the enthalpic and entropic elastic regimes, respectively, give \( {E}_o\approx {M}_w^{0.8} \). The Young modulus of biopolymer fibrillar networks is usually reported to scale as \( {E}_o\approx {M}_w^2 \) for lower average molecular weight 3 104 g/mol < Mw < 7 104 g/mol (Eldridge and Ferry 1954). The dependence on Mw of the elastic modulus of agarose hydrogels is expected to be lower for higher average molecular weight and higher polymer concentrations as the number of dangling ends not involved in the elasticity of the network becomes less (Normand et al. 2000).
Viscoelasticity of agarose hydrogels
The shear stress relaxation response of quasi-equilibrium agarose hydrogels was monitored in the linear regime when applying a low compressive strain ε ≈ 2% (Section 2.4). The characteristic viscoelastic time t2 at short timescale decreases from 2 min down to 16 seconds when increasing the agarose concentration 0.5 wt% < c < 7 wt% as the hydrogel becomes stiffer (Fig. 19). The retarded elastic response (G2 + G3)/G0 of about 10% to 15% for agarose concentration c > 1 wt% surprisingly takes on a much larger value (G2 + G3)/G0 ≈ 48% for a diluted 0.5 wt% agarose hydrogel (L0.5 sample in Fig. 19 and Table 4). Such a sharp increase in the apparent viscoelasticity of a diluted agarose hydrogel probably results from the buckling-induced aging of the sparsely connected network on long timescale and the gradual emergence of non-linear effects.
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Ed-Daoui, A., Snabre, P. Poroviscoelasticity and compression-softening of agarose hydrogels. Rheol Acta 60, 327–351 (2021). https://doi.org/10.1007/s00397-021-01267-3
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DOI: https://doi.org/10.1007/s00397-021-01267-3